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United States Patent |
6,091,242
|
Hanawa
|
July 18, 2000
|
Magnetic reasonance diagnosis apparatus
Abstract
An inversion pulse is applied to the subject in a static magnetic field. An
excitation pulse is applied after a delay time depending on the time
constant of the longitudinal relaxation of the spins of proton contained
in fat molecule from this inversion pulse. As a result, the spins of
proton contained in the fat molecule can be suppressed at high precision.
On the basis of the MR signal collected after this suppression, the
resonance frequency data of the spins of proton contained in water
molecule which is not suppressed or the data corresponding to this
resonance frequency, or the magnetic field distribution data of the static
magnetic field or the data corresponding to this magnetic field
distribution can be determined at high precision.
Inventors:
|
Hanawa; Masatoshi (Otawara, JP)
|
Assignee:
|
Kabushiki Kaisha Toshiba (Kawasaki, JP)
|
Appl. No.:
|
149447 |
Filed:
|
September 9, 1998 |
Foreign Application Priority Data
Current U.S. Class: |
324/307; 324/300; 324/309; 600/410; 600/412 |
Intern'l Class: |
G01V 003/00 |
Field of Search: |
324/309,307,300
600/410,112
|
References Cited
U.S. Patent Documents
5142231 | Aug., 1992 | Jensen et al. | 324/309.
|
Primary Examiner: Oda; Christine K.
Assistant Examiner: Shrivastav; Brij B.
Attorney, Agent or Firm: Nixon & Vanderhye, P.C.
Claims
What is claimed is:
1. A magnetic resonance diagnosis apparatus comprising:
means for applying an inversion pulse to the subject in a static magnetic
field, in order to selectively suppress one of spins of nuclide contained
in first molecule and spins of the same nuclide contained in second
molecule on the basis of the difference in the longitudinal relaxation
time, and applying an excitation pulse after a delay time corresponding to
the time constant of longitudinal relaxation of one of the spins of the
nuclide contained in the first molecule and the spins of the same nuclide
contained in the second molecule from the inversion pulse;
means for collecting MR signals from other one of the spins of the nuclide
contained in the first molecule and the spins of the same nuclide
contained in the second molecule; and
means for obtaining at least one of resonance frequency data of the other
one of the spins of the nuclide contained in the first molecule and the
spins of the same nuclide contained in the second molecule, data
corresponding to resonance frequency, magnetic field distribution data of
the static magnetic field, and data corresponding to magnetic field
distribution, on the basis of the MR signals.
2. A magnetic resonance diagnosis apparatus according to claim 1, wherein
the first molecule is water, the second molecule is fat, and the nuclide
is proton.
3. A magnetic resonance diagnosis apparatus according to claim 1, wherein
the delay time is set so that the longitudinal magnetized components of
the spins of the nuclide contained in the first molecule and the spins of
the same nuclide contained in the second molecule become substantially
zero in the center of the excitation pulse.
4. A magnetic resonance diagnosis apparatus according to claim 1, wherein
the delay time .DELTA.T is set to satisfy the following formula, supposing
the flip angle of the inversion pulse to be .theta., and the time constant
of longitudinal relaxation of one of the spins of the nuclide contained in
the first molecule and the spins of the same nuclide contained in the
second molecule to be T1:
1=(1-cos .theta.) exp (-.DELTA.T/T1).
5. A magnetic resonance diagnosis apparatus according to claim 1, wherein
the bandwidth of the inversion pulse is set in a relatively wide band, on
the basis of at least one of the timely fluctuations of intensity of the
static magnetic field and spatial fluctuations of intensity of the static
magnetic field.
6. A magnetic resonance diagnosis apparatus according to claim 5, wherein
the bandwidth of the inversion pulse is set in a relatively wide band,
including the fluctuation width of the resonance frequency of one of the
spins of the nuclide contained in the first molecule and spins of the same
nuclide contained in the second molecule, corresponding to the
fluctuations of the intensity of static magnetic field of about 5 ppm.
7. A magnetic resonance diagnosis apparatus according to claim 6, wherein
the bandwidth of the inversion pulse is set at 300 Hz or more when the
intensity of the static magnetic field is 1.5 tesla.
8. A magnetic resonance diagnosis apparatus according to claim 1, further
comprising:
means for applying at least one spoiler gradient magnetic field pulse in an
interval between the inversion pulse and the excitation pulse.
9. A magnetic resonance diagnosis apparatus according to claim 1, further
comprising:
means for applying a chemical shift selective pulse for selectively
exciting the other one of the spins of the nuclide contained in the first
molecule and the spins of the same nuclide contained in the second
molecule; and
means for controlling the center frequency of the chemical shift selective
pulse on the basis of the resonance frequency data or the data
corresponding to resonance frequency.
10. A magnetic resonance diagnosis apparatus according to claim 1, further
comprising:
plural shim coils;
means for supplying a current flowing to the plural shim coils; and
means for individually controlling the current flowing in the plural shim
coils depending on the magnetic field distribution data of the static
magnetic field or the data corresponding to this magnetic field
distribution.
11. A magnetic resonance diagnosis apparatus comprising:
means for suppressing one of spins of a nuclide contained in a first
molecule and spins of the same nuclide contained in a second molecule
depending on the difference in the longitudinal relaxation time;
means for collecting MR signals from other one of the spins of the nuclide
contained in the first molecule and the spins of the same nuclide
contained in the second molecule; and
means for determining at least one of the resonance frequency data of the
other one of the spins of the nuclide contained in the first molecule and
the spins of the same nuclide contained in the second molecule, the data
corresponding to this resonance frequency, the magnetic field distribution
data of the static magnetic field, and the data corresponding to this
magnetic field distribution data, on the basis of the MR signals.
12. A magnetic resonance diagnosis apparatus comprising:
a radio frequency coil for generating a radio frequency magnetic field;
a radio frequency coil driver for supplying a current flowing to the radio
frequency coil;
a receiver for receiving an MR signal through the radio frequency coil;
a controller for controlling the radio frequency coil driver for executing
a specified pulse sequence, in the pulse sequence, in order to selectively
suppress one of spins of a nuclide contained in a first molecule and spins
of the same nuclide contained in a second molecule depending on the
difference in the longitudinal relaxation time, having an inversion pulse
applied to the subject in a static magnetic field, and an excitation pulse
applied after a delay time depending on the time constant of longitudinal
relaxation of one of the spins of the nuclide contained in the first
molecule and the spins of the same nuclide contained in the second
molecule from this inversion pulse; and
a processor for determining at least one of the resonance frequency data of
the other one of the spins of the nuclide contained in the first molecule
and the spins of the same nuclide contained in the second molecule, the
data corresponding to this resonance frequency, the magnetic field
distribution data of the static magnetic field, and the data corresponding
to this magnetic field distribution data, on the basis of the MR signals.
13. A magnetic resonance diagnosis apparatus according to claim 12, wherein
the delay time is set so that the longitudinal magnetized components of
the spins of the nuclide contained in the first molecule and the spins of
the same nuclide contained in the second molecule may be substantially
zero in the center of the excitation pulse.
14. A magnetic resonance diagnosis apparatus according to claim 12, wherein
the bandwidth of the inversion pulse is set in a relatively wide band,
including the fluctuation width of the resonance frequency of one of the
spins of the nuclide contained in the first molecule and spins of the same
nuclide contained in the second molecule, corresponding to the
fluctuations of the intensity of static magnetic field of about 5 ppm.
Description
BACKGROUND OF THE INVENTION
It is known that the atomic nucleus containing an odd number of protons or
an odd number of neutrons has magnetic and hence generates a nuclear
magnetic dipole moment. When this nuclear magnetic dipole moment is placed
in a static magnetic field, the nuclear magnetic dipole moment makes a
rotary motion called precession at an angular frequency determined by the
product of the intrinsic magnetogyric ratio of the nucleus and the
intensity of the static magnetic field. In this state, when a rotating
magnetic field is applied to the nuclear magnetic dipole moment at this
angular frequency, the precession of the nuclear magnetic dipole moment
becomes gradually violent.
Regarding this motion in a rotating coordinate systems rotating at the same
angular frequency as in the rotating magnetic field, putting the z' axis
in the direction of static magnetic field, the nuclear magnetic dipole
moment is tilted from the z' axis toward the x'-y' plane. This tilting
angle generally is called the flip angle, which is determined by the
magnetogyric ratio, intensity of rotating magnetic field, and application
time of the rotating magnetic field.
When the rotating magnetic field is applied in the condition of the flip
angle of, for example, 90.degree., and then the rotating magnetic field is
stopped, the nuclear magnetic dipole moment returns gradually from the
x'-y' plane to the initial state aligned in the z' axis before application
of the rotating magnetic field while making precession. This process is
explained by two processes, that is, longitudinal relaxation process for
recovering the magnetized components in the static magnetic field
direction, and transverse relaxation process for attenuating the
magnetized components in the x'-y' plane. The longitudinal relaxation
process is also called the spin-lattice relaxation or T1 relaxation, and
its time constant is generally expressed as T1. The transverse relaxation
process is called the spin-spin relaxation or T2 relaxation, and its time
constant is T2.
Such magnetizing motion in the relaxation process can be observed by a coil
placed in the x'-y' plane. In other words, the precession of magnetization
induces a magnetic flux change in the coil, and therefore, according to
the Faraday's electromagnetic induction law, an electromotive force at the
aforementioned angular frequency is generated at both ends of the coil.
This electromotive force is the so-called magnetic resonance signal (MR
signal).
From the MR signal collected by utilizing such nuclear magnetic resonance
phenomenon, the spatial distribution of a specific nucleus and the state
of various molecules containing the nucleus can be observed.
To obtain a magnetic resonance image of high diagnostic ability, it is
important to detect the resonance frequency of the nucleus accurately and
enhance the spatial uniformity of static magnetic field.
Herein, to achieve the two objects, hitherto, as the preparatory steps for
imaging, the processes called frequency lock and shimming are executed.
The frequency lock is to specify the resonance frequency or center
frequency of the nuclide (since the resonance frequency has a certain
bandwidth, its central value (or peak value) is thus called
representatively). For instance, if the intensity of the static magnetic
field is 1.5 T, it may be actually 1.5 T.+-..alpha. owing to the drift of
the main magnet or other factors, and when the intensity of the static
magnetic field is deviated from 1.5 T, the resonance frequency of the
nuclide is deviated accordingly, and hence frequency lock is an
indispensable step. Without this step, the area may be different from the
region to be imaged, and other spin than aimed may be excited.
Shimming or active shimming is to correct spatial fluctuation of static
magnetic field (nonuniformity of static magnetic field). Nonuniformity of
static magnetic field occurs also in the presence of the object, and if it
is not corrected, various artifacts may be caused or undesired region may
be excited. In a typical example, therefore, the spatial magnetic field
distribution of the imaging region is determined, and the linear or
nonlinear gradient magnetic field for making it uniform is obtained, and
shimming is achieved by superposing it on the static magnetic field.
In the same nucleus, however, the intensity of the magnetic field that the
nucleus actually feels varies somewhat due to the effect of electrons
surrounding the nucleus, that is, the magnetic field shielding effect.
Since the state of electrons varies with the molecules containing the
nucleus, and therefore the resonance frequency is slightly deviated
depending on the molecules. This deviation is called the chemical shift.
For example, supposing the object nucleus to be proton (.sup.1 H), the
difference in chemical shift between water and fat containing it is
deviated by about 3.5 ppm as shown in FIG. 7. This 3.5 ppm corresponds to
about 224 Hz, supposing the static magnetic field intensity to be 1.5
tesla.
This chemical shift includes various artifacts, for example, deviation of
position of water and position of fat on the image, but, to the contrary,
it is attempted to utilize this chemical shift. Principal applications
include the chemical shift imaging for providing the image only for the
nucleus contained in a specific molecule, and MR spectroscopy for
presenting frequency spectrum of MR signal. From these data, for example,
a water image may be created, or various useful information relating to
metabolic functions, for example, the mode of compound produced by
metabolism can be obtained.
Such chemical shift imaging and MR spectroscopy are significantly
influenced by the non-uniformity of the static magnetic field. In
particular, the chemical shift selective pulse (CHESS pulse) widely used
in such chemical shift imaging or MR spectroscopy is likely to be
influenced by the non-uniformity of static magnetic field. This CHESS
pulse is adjusted in a relatively narrow bandwidth around the actual
resonance frequency so as to excite or invert selectively only the
specific nucleus contained in the specific molecule. For effective
function of the CHESS pulse, the so-called frequency lock is
indispensable, that is, the center frequency must be accurately adjusted
to the resonance frequency of the specific nucleus contained in the
specific molecule. Also, in order that the action the magnetization
receives from the CHESS pulse may not fluctuate depending on the location,
the current flowing in the shim coil must be adjusted to suppress spatial
variations of the strength of static magnetic field, that is,
non-uniformity of static magnetic field at, for example, less than 1 ppm,
and hence the magnetic field distribution is dynamically corrected, which
is known as dynamic shimming.
For frequency lock, the actually collected MR signal is Fourier
transformed, and from the obtained frequency spectrum, it is required to
measure accurately the true value of the resonance frequency of the object
nucleus. FIG. 1 shows a frequency spectrum obtained by Fourier transform
of the MR signal collected from the proton spins. Since the resonance
frequency Ffat of proton contained in the fat molecule is lower than the
resonance frequency Fwater of proton contained in the water molecule, the
lower one of the two peaks can be identified as Ffat and the higher one as
Fwater.
However, if one of fat and water is hardly present within the object slice,
only one peak appears in the frequency spectrum. Therefore, only two peak
frequencies cannot be judged to be either Ffat or Fwater.
The effect of shimming is exhibited only when performed along the accurate
magnetic field distribution. Therefore, the difference in chemical shift
between fat and water is a serious obstacle for accurate measurement of
magnetic field distribution.
BRIEF SUMMARY OF THE INVENTION
It is hence an object of the present invention to provide a magnetic
resonance diagnosis apparatus capable of measuring at least one of
resonance frequency data, its corresponding data, magnetic field
distribution data, and its corresponding data, at high precision, by
eliminating the error due to chemical shift.
According to the present invention, an inversion pulse is applied to the
subject placed in a static magnetic field, and after a delay time from
this inversion pulse depending on the time constant of one longitudinal
relaxation of the spins of the nuclide contained in a first molecule and
the spins of the same nuclide contained in a second molecule, and
excitation pulse is applied, and therefore one of the spins of the nuclide
contained in the first molecule and the spins of the same nuclide
contained in the second molecule can be suppressed at high precision. On
the basis of the MR signal collected after this suppression, the resonance
frequency data of the spins of the nuclide contained in the first or
second molecule not suppressed or the data corresponding to this resonance
frequency, or the magnetic field distribution data of the static magnetic
field or the data corresponding to this magnetic field distribution can be
determined at high precision.
Additional objects and advantages of the invention will be set forth in the
description which follows, and in part will be obvious from the
description, or may be learned by practice of the invention. The objects
and advantages of the invention may be realized and obtained by means of
the instrumentalities and combinations particularly pointed out
hereinafter.
BRIEF DESCRIPTION OF THE SEVERAL VIEWS OF THE DRAWING
The accompanying drawings, which are incorporated in and constitute a part
of the specification, illustrate presently preferred embodiments of the
invention, and together with the general description given above and the
detailed description of the preferred embodiments give below, serve to
explain the principles of the invention.
FIG. 1 is a diagram showing difference in chemical shift between proton
contained in water molecule and proton contained in fat molecule;
FIG. 2 is a structural diagram of a magnetic resonance diagnosis apparatus
in a preferable embodiment of the present invention;
FIG. 3 is a diagram showing a pulse sequence designed for measurement of
true value of resonance frequency of proton spins contained in water
molecule in the present embodiment;
FIG. 4 is a diagram showing a frequency bandwidth of CHESS pulse 61 in FIG.
3;
FIG. 5 is a diagram comparing a longitudinal relaxation curve of proton
spins contained in water molecule, and longitudinal relaxation curve of
proton spins contained in fat molecule, in order to show the interval T1
(fat) in FIG. 3;
FIG. 6A is a diagram showing a frequency spectrum obtained by Fourier
transform of MR signal collected from the pulse sequence in FIG. 3;
FIG. 6B is a diagram showing a frequency spectrum obtained by Fourier
transform of MR signal collected from the pulse sequence designed for
measurement of true value of resonance frequency of proton spins contained
in fat molecule, contrary to FIG. 3;
FIG. 7 is a diagram showing a pulse sequence designed for measurement of
magnetic field distribution in the present embodiment; and
FIG. 8 is a diagram showing other pulse sequence designed for measurement
of magnetic field distribution in the present embodiment.
DETAILED DESCRIPTION OF THE INVENTION
Preferred embodiments of the invention will be described below referring to
the drawings.
FIG. 2 shows a constitution of a magnetic resonance diagnosis apparatus
according to the present embodiment. A magnet assembly 1 includes a static
magnetic field coil 2, gradient magnetic field coils 3, and radio
frequency magnetic field coil 4 arranged near the space (imaging region)
for accommodating the subject.
The static magnetic field coil 2 is composed of normal conductive coil and
superconducting coil, and generates a static magnetic field in the imaging
region together with a static magnetic field coil driver 6. Herein, the
direction of the static magnetic field is defined to be the Z axis. The
gradient magnetic field coils 3 generate X axis gradient magnetic field, Y
axis gradient magnetic field, and Z axis gradient magnetic field,
individually together with a gradient magnetic field driver 14. The
gradient magnetic fields are overlaid on the static magnetic field.
A radio frequency oscillator 16 generates a radio frequency signal. The
frequency of this radio frequency signal is controlled by a controller 13.
A gate circuit 17 gates the timing of the radio frequency signal from the
radio frequency oscillator 16 in order to determine the pulse width of the
radio frequency pulse. The gate circuit 17 also modulates the frequency of
the radio frequency pulse in order to determine the center frequency and
the frequency bandwidth of the radio frequency pulse. The gate period is
controlled by the controller 13. The center frequency and the frequency
bandwidth of the radio frequency pulse are controlled by the controller
13.
An electric power amplifier 18 amplifies the radio frequency pulse from the
gate circuit 17. The amplified radio frequency pulse is supplied into a
radio frequency magnetic field coil 4 through a duplexer 5. As a result, a
radio frequency magnetic field pulse is generated from the radio frequency
magnetic field coil 4. The pulse period of the radio frequency magnetic
field pulse is same as in the gate period. The center frequency and the
frequency bandwidth of the radio frequency magnetic field pulse are same
as the center frequency and the frequency bandwidth of the radio frequency
pulse.
When receiving, an MR signal is induced in the radio frequency magnetic
field coil 4. This MR signal is amplified in a preamplifier 19, and is
detected of phase in a phase detector 20, and is stored in a waveform
memory 21.
A processor 11 processes the data stored in the waveform memory 21, and
obtains the following data.
1) Resonance frequency data of spins of proton contained in water molecule
(hereinafter called water spins)
2) Data corresponding to resonance frequency of water spins
3) Resonance frequency data of spins of proton contained in fat molecule
(hereinafter called fat spins)
4) Data corresponding to resonance frequency of fat spins
5) Magnetic field distribution data showing spatial distribution of
intensity of static magnetic field
6) Data corresponding to magnetic field distribution showing spatial
distribution of intensity of static magnetic field
7) MRI (magnetic resonance imaging) data
8) MRS (magnetic resonance spectroscopy) data
9) MRSI (magnetic resonance spectroscopic imaging) data
The aforementioned data 1) to 6) are utilized directly or indirectly in the
pulse sequence for execution for obtaining data 7) to 9). The pulse
sequence executed for obtaining the data 1) to 6) is called the
preparation pulse sequence, and the pulse sequence executed for obtaining
data 7) to 9) is called the main pulse sequence.
The aforementioned data 1) to 4) are used as fundamental data for adjusting
the center frequency and frequency bandwidth of the RF pulse, for example,
a slice selective pulse, chemical shift a selective pulse contained in the
main pulse sequence. The aforementioned data 5) and 6) are used as
fundamental data for adjusting the current flowing in the shim coil for
correcting the non-uniformity of static magnetic field of main pulse
sequence.
The display 12 is provided for displaying the data determined in the
processor 11.
The operation of the present embodiment is described below. First, terms
are defined below.
The excitation pulse is a RF pulse having a function of exciting
magnetization spins for generating transverse magnetized components. When
excitation pulse is applied, the magnetization spins are tilted by, for
example, 90.degree. about the x or y axis.
The refocus pulse is a RF pulse having a function of focusing the
transverse magnetized components of the spins dispersed by the transverse
relaxation phenomenon. When refocus pulse is applied, the spins are
rotated by, for example, 180.degree. about the x or y axis.
The inversion pulse inverts the polarity of the magnetization spins at the
position of longitudinal magnetization. In other words, it is a RF pulse
having a function of inverting the magnetization spins from +Z to -Z. When
inversion pulse is applied, the spins are rotated by, for example,
180.degree. about the x or y axis to be aligned in -Z.
FIG. 3 shows the preparation pulse sequence for obtaining data 1) or
2),that is, the preparation pulse sequence for obtaining the resonance
frequency of water spins or its corresponding value. This preparation
pulse sequence contains a pre-pulse for so-called fat suppression so that
the MR signal that is, in order words, the MR signal from the fat spins
may not be guided into the radio frequency magnetic field coil 4. As the
method of fat suppression, it is a main method to apply a gradient
magnetic field for dephase after selectively exciting only the fat spins
by the chemical shift selective pulse, but it cannot be employed because
accurate resonance frequency of fat spins is unknown, that is, it is
contrary to the defined condition that the center frequency and frequency
bandwidth in the chemical shift selective pulse cannot be optimized.
In other words, it is necessary to search a technique for realizing fat
suppression if the accurate resonance frequency of fat spins is unknown.
What is finally employed is a technique of suppressing fat spins on the
basis of the difference between the time constant T1 (fat) of longitudinal
relaxation of fat spins, and the time constant T1 (water) of longitudinal
relaxation of water spins.
First, an inversion pulse 61 is applied to the subject. This inversion
pulse 61 is not a slice selective pulse. The center frequency Ffat of the
inversion pulse 61 is, as shown in FIG. 4, set in the resonance frequency
of fat spins calculated according to Larmor's formula, from the intensity
of static magnetic field in calculation, magnetogyric ratio intrinsic to
proton spins, and chemical shift of fat spins.
The bandwidth .DELTA.F of the inversion pulse 61 is set in a relatively
wide bandwidth, on the basis of the timely fluctuations of the magnetic
field intensity and spatial fluctuations of the magnetic field intensity.
More specifically, the magnetic field intensity varies a maximum of 0.1
ppm per hour. The spatial variance of magnetic field intensity is 6 ppm at
maximum. In other words, the maximum fluctuation of resonance frequency of
fat spins is 5 ppm, and for example, at 1.5 tesla, fluctuation of 300 Hz
is assumed at maximum. Therefore, in the case of 1.5 tesla, by setting the
bandwidth .DELTA.F of the inversion pulse 61 at 300 Hz or more, allowing
time and spatial variations, almost all fat spins can be inverted.
Incidentally, if the object of suppression is water spins, the center
frequency Fwater of the inversion pulse 61 is set in the resonance
frequency of water spins calculated according to Larmor's formula, from
the intensity of static magnetic field in calculation, magnetogyric ratio
intrinsic to proton spins, and chemical shift (zero) of water spins. The
bandwidth .DELTA.F of the inversion pulse 61 may be 300 Hz or more same as
in the case of fat suppression.
Next to this inversion pulse 61, gradient magnetic field pulses for spoiler
63 to 65 are applied. As a result, if the flip angle by the inversion
pulse 61 is incomplete, by spoiling the transverse magnetized components
of fat spins generated by this, MR signal can be prevented from being
issued from fat spins.
After the gradient magnetic field pulses for spoiler 63 to 65, a first
excitation pulse 51 out of plural radio frequency magnetic field pulses
contained in the signal generation sequence, herein, the spin echo
sequence is applied together with a gradient magnetic field pulse for
slice selection 52. The center of this excitation pulse 51 is delayed from
the center of the inversion pulse 61 by time .DELTA.T.
This delay time .DELTA.T is set to satisfy the following formula (1) so
that the longitudinal magnetized components of fat spins may be
substantially zero in the center of the excitation pulse 51 as shown in
FIG. 5. Supposing the flip angle by the inversion pulse 61 to be .theta.,
and the time constant of longitudinal relaxation of fat spins to be
T1(fat), it is set to satisfy formula (1).
1=(1-cos .theta.) exp (-.DELTA.T/T1(fat)) (1)
For example, it is set at.DELTA.T=0.69 T1(fat).
Meanwhile, since the time constant of longitudinal relaxation of water
spins is slightly different from the time constant of longitudinal
relaxation of fat spins, in the center of the excitation pulse 51,
longitudinal magnetized components of water spins are present. When the
resonance frequency of water spins is present in the bandwidth of the
inversion pulse 61, water spins are inverted together with fat spins, but
in this case, as shown in FIG. 5, the longitudinal magnetized components
of water spins are always present in the center of the excitation pulse
51.
By thus setting the delay time .DELTA.T, water spins generate transverse
magnetized components by the excitation pulse 51, but fat spins do not
generate transverse magnetized components, that is, it is possible to set
the state in which MR signal is not delivered from the fat spins. When the
object of suppression is water spins, the delay time .DELTA.T is set at
the time determined by replacing T1(fat) of formula (1) with the time
constant T1(water) of longitudinal relaxation of water spins.
Successively to the excitation pulse 51, a refocus pulse 54 is applied
together with a gradient magnetic field pulse for slice selection 55, and
in the echo time, the MR signal (spin echo signal) from the water spins
only is sampled at a sufficiently high sampling frequency.
This echo signal is Fourier transformed in the processor 11. As a result, a
frequency spectrum as shown in FIG. 6A is obtained. Since the fat spins
are suppressed, in this frequency spectrum, only one peak corresponding to
the resonance frequency of water spins appears. Therefore, if fat is
hardly present in the object slice, one peak frequency can be identified
as the resonance frequency of water spins.
The resonance frequency of fat spins is determined by adding the frequency
corresponding to 3.5 ppm of chemical shift of the both, or 224 Hz in the
case of 1.5 tesla, to the measured resonance frequency of water spins.
When water spins are suppressed, as shown in FIG. 6B, the peak
corresponding to the resonance frequency of water spins does not appear on
the frequency spectrum, and only the peak corresponding to the resonance
frequency of fat spins appears. The resonance frequency of water spins is
determined by subtracting the frequency corresponding to 3.5 ppm of
chemical shift of the both, or 224 Hz in the case of 1.5 tesla, from the
measured resonance frequency of fat spins.
Incidentally, regardless of the existing state of fat and water in the
slice, both resonance frequencies can be measured. The frequency spectrum
(first frequency spectrum) is determined by the fat suppression pulse
sequence shown in FIG. 3. By the pure spin echo pulse sequence free from
fat suppression portion, the frequency spectrum (second frequency
spectrum) is determined. A third frequency spectrum is determined by
Fourier transform of the differential signal of the echo signal collected
from the fat suppression pulse sequence and the echo signal collected from
the pure spin echo pulse sequence. Depending on the case, as described
below, the apparition manner of peak of each frequency spectrum varies.
First case (both fat and water are present): In the first frequency
spectrum, one peak expressing the resonance frequency of water spins
appears. In the second frequency spectrum, a peak expressing the resonance
frequency of fat spins and a peak expressing the resonance frequency of
water spins appear. In the third frequency spectrum, one peak expressing
the resonance frequency of fat spins appears.
Second case (fat is absent and only water is present): In the first and
second frequency spectra, one peak expressing the resonance frequency of
water spins appears. In the third frequency spectrum, no peak appears.
Third case (water is absent and only fat is present): In the first
frequency spectrum, one peak expressing the resonance frequency of fat
spins appears. In the second and third frequency spectra, no peak appears.
According to this technique, regardless of the case, the resonance
frequency can be determined by distinguishing water and fat.
According to thus obtained data 1) to 4), the center frequency and
frequency bandwidth of the chemical shift selective pulse (RF pulse) in
the main pulse sequence are adjusted. Therefore, only the proton contained
in water or fat molecule can be imaged.
Next is explained the preparation pulse sequence for determining the data
5) and 6),that is, the magnetic field distribution or the corresponding
data. FIG. 7 shows an example of this preparation pulse sequence. In FIG.
7, the same pulses as in the preparation pulse sequence in FIG. 3 are
identified with same reference numerals. This preparation pulse sequence
starts with the inversion pulse 61 same as in the preparation pulse
sequence in FIG. 3, and after the delay time .DELTA.T from the inversion
pulse 61 through spoiler pulses 63-65, an excitation pulse 51 is applied
together with a gradient magnetic field pulse 52 for slice selection.
Next, to provide the MR signal with spatial information, a gradient
magnetic field pulse for phase encoding 57 is applied. Consequently, by an
alternated gradient magnetic field 58, gradient echoes 71,72 are collected
in series.
Since the phase of MR signal is determined depending on the integration of
intensity of magnetic field being experienced, the phase difference
between the gradient echoes 71 and 72 differs, in the location where the
intensity of static magnetic field is different, depending on the
difference in intensity. In other words, the spatial distribution data of
the phase difference is given as the data corresponding to the magnetic
field distribution. A phase difference of echo appears of
.DELTA..theta.=.gamma..DELTA..beta..multidot..DELTA.t. .DELTA.t is an
interval between peaks of echo 71 and 72. Hence, .DELTA.B of each pixel is
determined.
On the basis of thus obtained magnetic field distribution or its
corresponding data, by adjusting the current flowing in the shim coil in
the period of main pulse sequence, the uniformity of static magnetic field
can be enhanced. As a result, the information relating to the chemical
shift is obtained at high precision.
In the preparation pulse sequence shown in FIG. 8, the magnetic field
distribution or its corresponding data can be determined. In FIG. 8, same
pulses as in the preparation pulse sequence in FIG. 3 are identified with
same reference numerals. This preparation pulse sequence starts with the
inversion pulse 61 same as in the preparation pulse sequence in FIG. 3,
and after the delay time .DELTA.T from the inversion pulse 61 through
spoiler pulses 63-65, an excitation pulse 51 is applied together with a
gradient magnetic field pulse 52 for slice selection. Next, to provide the
MR signal with spatial information of two axes, two phase encode pulses
59, 60 are applied, and two axes in the slice are encoded. At echo time,
MR signal (echo) is collected. The frequency of echo signal depends on the
resonance frequency of water spins of each location. Since the resonance
frequency of water spins depends on the external magnetic field, the
spatial distribution data of echo signal frequency is given as the data
corresponding to the magnetic field distribution.
Not limited to the illustrated embodiments, of course, the invention may be
changed and modified in various forms.
Additional advantages and modifications will readily occurs to those
skilled in the art. Therefore, the invention in its broader aspects is not
limited to the specific details and representative embodiments shown and
described herein. Accordingly, various modifications may be made without
departing from the spirit or scope of the general inventive concept as
defined by the appended claims and their equivalents.
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